EP3085303B1 - Système et procédé de visualisation de données d'électrophysiologie - Google Patents

Système et procédé de visualisation de données d'électrophysiologie Download PDF

Info

Publication number
EP3085303B1
EP3085303B1 EP15202606.8A EP15202606A EP3085303B1 EP 3085303 B1 EP3085303 B1 EP 3085303B1 EP 15202606 A EP15202606 A EP 15202606A EP 3085303 B1 EP3085303 B1 EP 3085303B1
Authority
EP
European Patent Office
Prior art keywords
electrodes
catheter
electrode
sequence
relative
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP15202606.8A
Other languages
German (de)
English (en)
Other versions
EP3085303A1 (fr
Inventor
Thomas Michael Severino
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Biosense Webster Israel Ltd
Original Assignee
Biosense Webster Israel Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Biosense Webster Israel Ltd filed Critical Biosense Webster Israel Ltd
Publication of EP3085303A1 publication Critical patent/EP3085303A1/fr
Application granted granted Critical
Publication of EP3085303B1 publication Critical patent/EP3085303B1/fr
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/339—Displays specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
    • A61B5/283—Invasive
    • A61B5/287—Holders for multiple electrodes, e.g. electrode catheters for electrophysiological study [EPS]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/333—Recording apparatus specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7246—Details of waveform analysis using correlation, e.g. template matching or determination of similarity

Definitions

  • This invention relates generally to visualization of electrical activity of a patient, and more particularly to spatial visualization of electrophysiology data for a patient as detected by a catheter.
  • Cardiac arrhythmias are the leading cause of death in the United States.
  • electrical acquisition signals are conducted in an orderly way through the atrium and into the ventricle, passing each point in the heart only once in each heart cycle.
  • Electrical acquisition signals at different locations in the heart are well correlated, taking into account normal propagation delays from one region of the heart to another.
  • the atrial muscle fibers contract in proper synchrony to pump blood through the atrium.
  • the electrical conduction system of the heart provides the rhythm, or sequence of contraction of the heart muscle, so it may most efficiently pump blood to the rest of the body. Electrophysiologists study the conduction system to diagnose and treat abnormal heart rhythms, known as arrhythmias. It is desirable to provide methods and equipment that assist physicians with diagnosing abnormal heart rhythms, as well as gauging the success of treating these arrhythmias through ablation therapies.
  • WO95/10225 describes systems and methods to sense electrical events in heart tissue to identify the location of an arrhythmogenic focus for ablation.
  • the systems and methods establish a contact site between heart tissue and a curvilinear electrode array (e1-e4 or E1-E4).
  • the systems and methods monitor signals representing electrical events sensed by the electrodes in the contact site. The signals are displayed as graphic information that represents the time sequence in which the electrodes sense a given electrical event.
  • Cardiac tissue as it relates to the heart's electrical conduction system, has several important properties.
  • a cardiac cell can receive electrical stimulus.
  • it can respond to this stimulus or activate.
  • cardiac cells they contract, causing the heart to squeeze and pump blood.
  • this activation is referred to as depolarization. It is a chemical process in the cell. Once depolarized, the cell needs time, a few milliseconds, to recover. During this repolarization phase, the cell is said to be refractory, meaning it has not fully recovered and cannot yet receive another stimulus.
  • cardiac cells can propagate that electrical signal; that is, once stimulated, they can in turn stimulate the cells next to them.
  • cardiac cells are activated sequentially from an initial point of stimulation, propagating outward, across the heart chamber.
  • the refractoriness of cells just stimulated keeps the wave of depolarization from moving backwards; thus the wave continues forward across cardiac tissue or wall of a heart chamber in an organized fashion.
  • the "pebble-in-a-pond” analogy is often used to describe this; the ripples move outward in an orderly manner from a singular point of stimulation.
  • some anatomical structures such as heart valve openings and vessel ostia, will form obstacles for the wave of depolarization to navigate.
  • scars from cardiac surgery or damaged heart muscle do not conduct either, and the wave must make its way around the outside edge of these as well.
  • a normal heart beat with a normal electrical pathway starts at the Sinoatrial Node near the top of the right atrium (it is the SA node that has those cells with automaticity) and propagates across the right and left atria, causing them to contract and fill the ventricles with blood (a series of one-way valves in the heart prevents the blood from flowing backwards).
  • the upper and lower chambers are divided by the atrioventricular septum which is made of membranous tissue that does not conduct electrical signal.
  • the wave of depolarization cannot, in a normal heart, simply continue straight across from the atria to the ventricles. This is regulated by tissue at the one electrical channel connecting them.
  • This collection of cardiac cells called the AV node, has additional properties that cause it to delay depolarization, allowing the atria to completely contract. It then sends the electrical signal straight to the ventricle apices where the wave of depolarization across the ventricles results in an efficient contraction that sends blood to the lungs and the rest of the body.
  • the delay between the atrial and ventricular depolarization causes the distinct "lub-Dup, lub-Dup" sound of the heart.
  • Electrophysiologists use electrode-tipped catheters placed at various locations in the heart to study its electrical conduction system in order to diagnose cardiac arrhythmias. They generally use well-established methods.
  • the catheters are long thin, plastic tubes with wires inside running to a series of evenly-spaced electrodes or, more commonly, pairs of electrodes at the distal end which are used to record the local activation at that discreet location in the heart.
  • a pair of electrodes close together will measure just the electrical activity at that small piece of tissue.
  • a recording system processes these electrograms and displays them on a monitor in real-time and also allows the user to freeze and review them. This allows the user to measure and compare the difference in timing of all the electrograms from the various locations at one moment in time in order deduce the current activation sequence and make a diagnosis.
  • Multipolar catheters are very helpful in analyzing a wave of depolarization across a particular piece of tissue.
  • endocardium the inside wall of the heart
  • the delay in activation from one end to the other will result in a slanted pattern of electrical activations .
  • the wave of depolarization crosses poles 1-2 of this catheter first. A few milliseconds later it crosses electrodes (or "poles") 3-4, then 5-6, and so forth, all the way to poles 19-20, which it crosses last.
  • poles 1-2 are said to be “earliest,” and poles 19-20 are said to be “latest.”
  • FIG. 2B shows the resulting electrograms.
  • the electrogram of poles 1-2 are earliest on the timeline, with poles 2-3 deflecting a few milliseconds later and poles 19-20 the latest.
  • a wave of depolarization moving in the other direction that crosses poles 19-20 first, followed by poles 17-18, 15-16, and so forth to poles 1-2, wherein poles 19-20 are earliest and poles 1-2 are latest, the visual pattern would be formed by electrograms slanting the other way.
  • Mappings systems discussed later, describe the timing of electrical activation as a graphical representation in terms of a color scale, where red represents earlier activation and purple represents later activation.
  • the electrograms When the multipolar catheter is oriented across the wave of activation, or if there are two intersecting waves of activation, however, the electrograms will have a convex or concave visual pattern to them.
  • FIG. 3A the wave crosses the distal and proximal poles 1-2 and 19-20 first, simultaneously, and passes poles 9-10 and 11-12, in the middle, last.
  • the electrograms in FIG. 3B reflect this and form a concave visual pattern.
  • the resulting electrograms' visual pattern would show a convex curve, as shown in FIG. 3C, with poles 9-10 and 11-12 early and poles 1-2 and 19-20 late.
  • Arrhythmias in general, can be categorized broadly as focal, reentrant, or disorganized. Focal arrhythmias have a single point of origin. A small group of cardiac cells away from SA node has gained the property of automaticity and depolarize at a fast rate. Since they activate faster than the SA Node, the cells there do not depolarize on their own; the SA Node is "suppressed”. Atrial Tachycardia is an example of this. The goal of therapy for this type of arrhythmia is to locate this group of cells depolarizing on their own and deliver localized RF energy (via the tip of an ablation catheter positioned at the site) to "ablate" or destroy them.
  • Reentrant arrhythmias in contrast, do not have a single point of origin.
  • the properties of depolarization, repolarization, and refractoriness can enable a situation where the driving activation pattern forms a loop around a neutral, non-conducting structure such as a heart valve or surgical scar.
  • the wave of depolarization takes it around the neutral structure, either clockwise or counterclockwise, in a circle.
  • the wave of depolarization returns to tissue that had just activated as it made the previous loop, that tissue is now past its refractory period and is ready to be stimulated again, in this case by the return wave.
  • the arrhythmia continues on this way, around and around, indefinitely.
  • Atrial Flutter is a very common reentrant arrhythmia revolving around the tricuspid valve in the right atrium.
  • the therapeutic strategy for reentry is to ablate a line of tissue (again, by means of an ablation catheter) from the neutral structure in the center of the loop to another, nearby neutral structure, thus creating a non-conducting lesion or "line of block" that disrupts the arrhythmia.
  • electrograms provided by positioned catheters are helpful in diagnosing an arrhythmia, more precise information is often needed to fully understand the abnormal activation pattern and target the appropriate area for the therapeutic phase of the study, which commences after the diagnosis is made. In many cases, a detailed sampling of electrograms over much or all of the endocardial surface of one or more heart chambers is required.
  • Electroanatomic mapping systems have been developed to (1) clearly define the endocardial anatomy as a 3D virtual model, (2) record and catalog sampled electrograms, (3) display the activation sequence (or other data) compiled from recorded electrograms on the virtual model, (4) track and display in real-time the current location of electrode catheters in the heart by projecting accurate representations of them into the virtual environment, and (5) record precise locations of sites of interest such as places where RF energy has been applied.
  • Mapping of the heart or a region thereof typically involves using a mapping catheter with tip and proximal electrodes to record electrical activity in the region of interest.
  • the catheter is moved along the wall of the endocardium during which precise locations and their corresponding electrograms are recorded.
  • the three-dimensional anatomic map is created or developed in real-time.
  • LATs local activation times
  • the LAT of each point is the interval between the beginning of the local electrogram of the mapping catheter and the reference signal.
  • the LATs are described in terms of color-red representing the earliest activation so far recorded and purple representing the latest-and applied to an anatomical map of the region of interest to create an activation , or LAT, map.
  • Each new acquisition, or "point,” updates the map until a complete--or at least sufficient--understanding of the activation sequence is presented.
  • FIG. 5 shows a series of new LAT as they are added to a map. Note that the anatomy has already been defined in this example and that the colors update as new data is recorded. The final image shows that a single focal site of activation has been located near the top of the chamber.
  • a sample completed LAT map of Atrial Flutter is shown in FIG. 7A .
  • the red-to-purple color pattern forms a clockwise loop around the tricuspid valve annulus (outlined by a green border), which has been cut out of the map.
  • the mapping/ablation catheter shown in white, two additional electrode catheters in a darker green, and the site of ablation shown as brown circles, are also visualized.
  • a completed LAT map can be visualized as a "propagation map" where the activation sequence on the map is played by the mapping system as an animation, showing the spread or propagation of electrical activation across the mapped region of interest each time it repeats.
  • This can be a very helpful, dynamic alternative to visually following the rainbow scale of activation around a static LAT map where very slight, yet potentially important changes in color shade, may be missed.
  • FIG. 6 shows a series of screen captures from a propagation map animation of the focal activation sequence shown in FIG. 5 .
  • the wave in color red of depolarization moves in time across the chamber shown in color blue.
  • the animations loop continually so the wave can be studied again once it plays through.
  • a "window of interest” for assigning activation times on the mapping catheter is selected. This is a time interval relative to an electrogram of a catheter in a fixed location or body surface that has been chosen as “timing reference.” Only those activation times falling within this window are acquired.
  • the WOI serves to limit the choice of electrograms to be measured to only those of the current heartbeat or cardiac cycle.
  • a WOI too wide might include the next or previous cycles.
  • the WOI can also be used in certain situations to exclude extra recordings on the mapping catheter electrogram such "stimulus artifact" from a pacing device, or "farfield signals", including electrograms from another chamber or region that have been detected by the mapping catheter.
  • the system searches for an electrogram on the mapping catheter channel within the WOI.
  • a time interval (in milliseconds) between the detected electrograms and the electrogram of the timing reference is calculated. This is recorded as the LAT or local activation time of that point.
  • the timing of these locations varies with how early or late the wave of depolarization crossing the catheter at each particular location is, while in the current heart rhythm. So, the electrograms appear earlier or later compared to those of reference catheter, which remains fixed and, therefore, has the same timing of its electrograms every beat. For this reason, the LATs measured at each new point varies.
  • LATs The points with the lowest, or most negative, LATs are considered earliest and appear in colors red and orange on the LAT map; conversely those with higher or less-negative activation times are later and shade their areas of the map in colors blue and purple. It is the concept of the fixed reference catheter and its "timing reference" that allows the mapped points of many different heartbeats with the same activation sequence to be compiled into a comprehensive LAT map showing the activation sequence of one representative cardiac cycle.
  • the mapping system may also include visualization of "non-sensor-based catheters" present in the region of interest.
  • catheter visualization may display localized electrodes of those catheters, wherein "localization” (location/position detection of electrodes) is obtained through impedance or current-based measurements. For example, impedance is measured between electrodes affixed to the catheter and electrodes placed on the body surface. The position of the catheter and its electrodes is then derived from the impedance measurements.
  • Methods for impedance-based position sensing are disclosed, for example, in U.S. Pat. No. 5,983,126 to Wittkampf , in U.S. Pat. No. 6,456,864 to Swanson , and in U.S. Pat. No. 5,944,022 to Nardella .
  • FIG. 7A is a sample activation map generated by the CARTO 3 mapping system of a right atrium RA of a patient's heart, with visualization of three localized catheters.
  • the ACL technology is responsive to movement of the electrodes of the catheters and therefore updates the image of the electrodes in real time to provide a dynamic visualization of the catheters and their electrodes correctly positioned, sized, and oriented to the displayed map area on the CARTO 3mapping system.
  • the catheter visual representations therefore respond to being repositioned by the physician, dislodging from position, and subtler movements such as those caused by the patient's own breathing pattern.
  • This dynamic movement of the catheter images stands in contrast to the 3-D maps themselves, which are created from a set of recorded locations and are, thus, static.
  • FAM Fast Anatomical Mapping
  • the electrophysiologist may choose to "remap,” in which case the geometry only of the current map is copied to a new map file and new data points in the new heart rhythm may be acquired to color in this "blank canvas.”
  • remapping may take as long to create as the original map, as the sensing catheter is moved from location to location to acquire a new set of LATs.
  • the electrophysiologist may choose not to remap but merely refer to the electrograms of properly positioned multipolar catheters (for example, see FIGS. 2B and 3B ), which, as mentioned earlier, are typically displayed on a recording device during an ablation procedure to provide additional data for use by the electrophysiologist. Electrograms may be particularly informative for those regions or chambers of the heart where there are well-established, standard catheter positions as well as established ablation patterns. An atrial flutter ablation procedure is one of the simplest examples of this. As briefly mentioned earlier, reentrant signals of atrial flutter in the right atrium typically have a circuitous path that is clockwise or counterclockwise around the tricuspid valve annulus TVA. FIG.
  • FIG. 7A shows a map of clockwise atrial flutter created using FAM and a dual-purpose, sensor-based mapping and ablation catheter.
  • the red-to-purple color pattern in this map can be traced clockwise around the valve (center circular cutout with thin green border) from the red area in the upper corner all the way around in a loop to the purple area returning to the starting point (CARTO 3 places the brown "early meets late line” into the map automatically between red and purple points).
  • Only one cardiac sequence is described by the map; in reality the wave of depolarization continues around and around in a continuous loop around the TVA.
  • FIG. 7A three catheters are visualized.
  • Catheters for this procedure typically include a nonmagnetic, current-based sensing "Duo-deca” multipolar catheter (in green) that enters the right atrium RA from the IVC and is generally positioned in a loop just outside the TVA. Its electrograms, therefore, help describe how the electrical activation is moving around the tricuspid valve. Longer versions of this catheter (actually, ones with more widely-spaced electrode pairs), like the one pictured, can extend across the floor of right atrium (the cavotricuspid isthmus) and into the coronary sinus ostium. A properly positioned Duo-Deca catheter produces a very distinct "slanted" electrogram patterns in atrial flutter (see for example, FIG. 2B ).
  • the direction of the slant indicates whether it is clockwise or counterclockwise atrial flutter (for example, clockwise in FIG. 2B ). Also visible in this map is the distal tip of a nonmagnetic, current-based HIS catheter (in green) protruding through the TCV from the right atrium RA into the right ventricle RV, and, of course, the magnetic sensing mapping and ablation catheter (in white), shown protruding from the IVC at the cavotricuspid istmus.
  • a nonmagnetic, current-based HIS catheter in green
  • the magnetic sensing mapping and ablation catheter in white
  • the typical ablation pattern for treating atrial flutter is an ablation line across the cavotricuspid isthmus CVI (at the floor of the heart), forming a "line of block" between the tricuspid valve TCV and the inferior vena cava IVC.
  • the map in FIG. 7A shows this as well, as brown circles on the floor of the heart marking ablation sites.
  • pacing delivering external electrical stimulus
  • the electrograms' visual pattern will either be a slanted line indicating the line of block is complete and the wave of activation must travel all the way around the valve to depolarize the tissue on the other side of it, or a curved line which suggests that, in addition to traveling up and around the valve, a wave of depolarization is also moving right across the ablation line.
  • FIG. 7B is a map of the same procedure, made during pacing to demonstrate a complete line of block.
  • the pacing stimulus is being delivered to an electrode pole just to right of the ablation line in the color red area of the map.
  • One can trace the resulting activation sequence by following the colors of the rainbow in sequence (red, orange, yellow, green, blue, and purple) starting with red and moving up and around the valve in a counterclockwise fashion all the way to the purple area just to the left of the ablation site, which is the latest tissue activated in the chamber during this pacing maneuver.
  • the map indicates that the line of block is indeed complete.
  • the electrograms of the Duo-deca catheter, from the proximal poles to the ones just leftward of the ablation line would have a slant pattern similar to those shown in FIG. 2C.
  • FIGS. 8A and 8B show another example of using the same pacing maneuver to confirm that the ablation line in the CVI is complete.
  • the activation pattern in FIG. 8A where the wave of depolarization, as evidenced by the red-to-purple color pattern of the map, shows activation moving from the red area (at the lower right of the map) not only up and around the top of valve, but also across the ablated line and the floor of the heart, as indicated by the green areas both at the roof and to the left of the ablation line.
  • the latest area of activation in purple is the far wall (at the left of the map). This "split" evidenced by two different green areas shows that there was not a complete line of block and that more ablating was necessary.
  • Electrograms of a successful block at the isthmus reveal one or more diagonal lines , each having the same or similar slope, such as item D in FIGS. 9A and 9B .
  • electrograms of breakthroughs through incomplete blocks often reveal two diagonal lines with opposite slopes which form either a convex or concave shape depending on the location of the pacing signal, such as items D1 and D2 in FIGS. 9C and 9D .
  • the electrograms in FIG. 9A describe the electrograms generally expected when pacing from the right side of a complete ablation line as in FIGS. 7B and 8B .
  • the concave shape of the electrograms in FIG. 9D indicates the situation in FIG. 8A , where the line of block is not complete ( FIGS.
  • FIGS. 10A-10D schematically represent the right atrium with anatomical features of the coronary sinus CS, the superior vena cava SVC and the inferior vena cava IVC. These figures illustrate the locations of the catheters CT and the paths P of the respective electrograms of FIGS. 9A-9D .
  • FIGS. 10A and 10B the earliest activation site S and the ablation line A are also shown.
  • FIGS. 10C and 10D the breakthrough due to an incomplete ablation line B is shown.
  • the DuoDeca catheter shown in FIG. 7B has more widely-spaced poles-giving a longer span of coverage-than other catheters of the same type. This catheter sits with its poles 1-2, 3-4 and 5-6 actually across the ablation line. While the electrograms in FIG. 9A-9D represent a more standard catheter with all the distal poles positioned to the left of the line, the electrophysiologist will have to know and consider the anatomical location of each catheter and its electrodes when analyzing the EGM pattern. The precise electrogram pattern for situation in FIG. 7B is shown in FIG. 11 .
  • AF atrial fibrillation
  • AF atrial fibrillation
  • a very common, but rather technically challenging, treatment for AF is a pulmonary vein isolation procedure (PVI), where the cardiac tissue around the ostia of each of the four pulmonary veins in the left atrium is ablated to create a circular line of block preventing these aberrant signals from entering the chamber.
  • PV pulmonary vein isolation procedure
  • FIG. 12 shows typical left-atrial anatomy with the four pulmonary veins shown in bright colors yellow (right superior), orange (right inferior), purple (left superior) and pink (left inferior).
  • the red structure is the left atrial appendage.
  • the tip of the mapping/ablation catheter as well as brown "point tags" marking ablation sites near the left superior pulmonary veins.
  • a lasso catheter in royal blue
  • a lasso catheter can sit with its distal loop in a pulmonary vein (represented by pink “webbing") with its electrodes in contact with an inner circumference of the vein.
  • the lasso catheter is visualized in an anatomical (anatomy only) CARTO map of the left atrium (the veins have been made transparent by the "webbing").
  • Other catheters and pink dots marking the current progress of the ablation are also visible.
  • the size or diameter of the distal loop is adjusted so that the loop and electrodes make adequate contact along the entire inner circumference of the vein in order to sense any aberrant or pacing signals that pass the loop traveling from the LA into the vein or from the vein into the left atrium usually in normal sinus rhythm.
  • Three-dimensional mapping with hybrid localization technology reveals the position of the catheter distal loop and electrodes.
  • the distal loop may be positioned randomly with its distal and proximal electrodes in any radial orientation.
  • changing the loop diameter to fit properly will also change the association of the loop's distal and proximal electrodes-poles may overlap in small veins or there may be a gap in large veins.
  • FIG. 13 is an example of overlapping electrodes on the lasso catheter. For these reasons, the electrograms alone may reveal which pole(s) are acquiring and the sequence of acquisition but not how this actually correlates to the anatomy itself.
  • the electrophysiologist must cross-reference the electrograms with the 3-D map and the visualized Lasso catheter in order to ascertain the location of acquiring pole(s) relative to the anatomy and hence the location of breakthrough(s) in the ablation line for placement of the ablation catheter.
  • the procedure is a treatment for AF, it is usually performed in normal sinus rhythm to help better gauge the success of lesion formation.
  • the electrogram pattern will change on the lasso catheter.
  • the sections that have yet to be ablated will have earlier corresponding electrograms.
  • the ablation of a pulmonary vein is complete when the wave of depolarization across the heart chamber (in the patient's normal heart rhythm) is blocked from entering the vein, and electrograms disappear completely from the Lasso catheter sensing from inside the vein. This process is repeated for each of the four pulmonary veins.
  • mapping/ablation catheter Due to the technical challenge of positioning the mapping/ablation catheter with sufficient contact to create durable lesions at each location around each pulmonary vein ostium, multiple ablations at the same locations are frequently required, and continual analysis of the Lasso electrograms is critical.
  • the electrograms are studied on the recording system to determine the electrode to target, and then those electrodes are located on the visualized lasso catheter in the map.
  • Mapping systems are very useful for this procedure. Knowledge of each patient's particular anatomy, and especially the orientation and position of the catheters inside it, are crucial. Marking sites of ablation is also very important. However, activation mapping is rarely done. This is because the activation sequence inside each pulmonary vein continuously changes while ablating, and this renders any map made useful for only a brief period of time before a remap is required.
  • the Lasso catheter In addition to the changing activation sequence, the Lasso catheter commonly falls out of position or gets dislodged while trying to maneuver the mapping/ablation catheter around in the same space. Repositioning it almost always results in a slightly or greatly different radial orientation than before, meaning its electrodes now represent a different location, and the electrograms and their corresponding positions in the map must be reassessed. For these reasons the following process must be repeated numerous times per procedure. First, once in proper position, the Lasso's electrograms are recorded and analyzed on the recording system. Next, a particular pole is named the current target for ablation. Then the electrophysiologist determines where that pole is located on the catheter image on the mapping system.
  • a system and method for real-time visualization of electrode activation on a multi-electrode catheter so a user can instantly recognize signal acquisition by electrodes, including a sequence of electrode acquisition, without reference to electrograms or a 3-D map or wait for any other information.
  • the system and method need not consider any timing reference and may function independently of any mapping or acquisition/propagation maps of any mapping system.
  • the system and method may provide visualization of electrode acquisition on a 3-D activation map with LATs information and catheter and electrode localization so that location of any and all acquiring electrodes relative to the mapped region is revealed.
  • the present invention includes methods and systems for visualization of electrophysiology information, including intracardiac electrical signals sensed by a catheter.
  • the visualization includes a display of continuous propagation of a catheter's electrogram.
  • An activation sequence is displayed in cine format in realtime or near-realtime and advantageously presented graphically and objectively in the conventional workspace in which an electrophysiologist is already viewing for catheter positioning.
  • the electrophysiologist may view, for example, an ablation block on a graphical image of a multi-polar "Halo” or “DuoDeca” catheter, earliest activation in a pulmonary vein on a graphical image of a multi-polar "Lasso” catheter, a wave of propagation across a graphical image of a multi-polar "PentaRay” catheter, or a general activation of the coronary sinus on a multi-polar linear catheter.
  • the visualization naturally indicates direction of propagation.
  • the present invention is directed in a first aspect to a method for visualization of electrophysiology information sensed by electrodes on a catheter, as defined in appended independent claim 1.
  • the method comprises, inter alia, recording times of electrode signal acquisition, designating a reference electrode signal acquisition, assigning a relative time to each recorded time of electrode signal acquisition relative to the reference electrode signal acquisition, identifying the electrodes with signal acquisition, correlating assigned relative times to identified electrodes to generate a sequence of electrode signal acquisitions, and generating a visual representation of the sequence of electrode signal acquisitions with a graphical image of the electrodes, wherein individual electrodes are visually marked to represent the sequence of electrode signal acquisitions.
  • the methods include generating a visual representation with a plurality of images shown in series to represent a progression of the sequence of electrode signal acquisitions.
  • each image shows a different electrode visually marked, or each image shows at least one different electrode visually marked.
  • the catheter has shaft sections extending between adjacent pairs of electrodes
  • the methods further includes assigning a relative time to each shaft section in accordance with relative times of its adjacent pair of electrodes, and correlating the relative time of each shaft section with the relative times of its adjacent pair of electrodes, wherein the visual representation includes a series of graphical images of the shaft sections displayed in cine format, and individual shaft section is visually marked in the series of graphical images in accordance with the sequence.
  • the methods include adjusting time scale of the visual representation in response to a user's selected time scale and/or adjusting or limiting the ratio of visual representations to actual cardiac cycles in order to facilitate ease of viewing and avoid overlapping sequences of electrode acquisitions.
  • the catheter has a plurality of electrodes, wherein each electrode is adapted to acquire electrical signal.
  • the catheter includes shaft subsections, each shaft subsection extending between an adjacent pair of electrodes, and the method further includes assigning a relative time to each shaft section in accordance with relative times of its adjacent pair of acquiring electrodes, and correlating the relative time of each shaft section and the relative times of its adjacent pair of acquiring electrodes, wherein the generating a visual representation includes providing a graphical image of each shaft section, and visually marking individual shaft sections in accordance with the sequence.
  • each shaft subsection is assigned a weighted relative time.
  • the weighted relative time may depend on location of shaft subsection between the adjacent pair of acquiring electrodes.
  • the electrodes acquiring electrical signal are identified by their lead wires.
  • the present invention is also directed to a system for collecting and visualizing electrophysiology information, as defined in appended independent claim 17.
  • the system includes, inter alia, a catheter with electrodes adapted to acquire signals, a signal processing unit configured to receive intracardiac signal acquisitions by a plurality of electrodes, and identify the electrodes with intracardiac acquisitions, a timer configured to time the intracardiac signal acquisitions and identify a reference time to an earliest intracardiac signal acquisition, a control unit configured to assign relative times to the intracardiac signal acquisitions relative to the reference time and to correlate assigned relative times to identified electrodes to generate a sequence of signal acquistions, and a display configured to display the sequence of signal acquisitions in a graphical image of at least the electrodes.
  • the display is configured to display the sequence of signal acquisitions in a graphical image of at least the electrodes.
  • the visual display of the activation sequence may include graphically highlighting the acquiring electrodes and/or shaft sections therebetween by a variety of indicia, for example, color, transparency, size, and/or boldness.
  • the electrodes of one or more catheters may be highlighted in this manner, as desired or appropriate.
  • the present invention is directed to a system and method for real-time visual portrayal of an acquisition sequence of electrodes on a catheter, in particular, real-time visual portrayal of acquisition sequence of electrodes acquiring local activation signals for generating electrograms of a heart.
  • the visualization of electrode acquisition sequence includes images of the catheter and its electrodes, and visual indicia of electrical propagation along at least an electrical sensing portion of the catheter, including, for example, visual indicia that distinguish acquiring electrode(s) from nonacquiring electrode(s) in real time.
  • the images include visual indicia of electrical propagation along electrical sensing portions of the catheter, and nonelectrical sensing portion, including, for example, acquiring electrodes and nonconductive tubing extending therebetween.
  • the visualization of the electrode acquisition sequence includes images of the catheter and its electrodes, superimposed on a heart chamber map, wherein the visualization is dynamic and in real-time corresponding to movement of the catheter in the heart chamber and the heart chamber map is in 3-D and provides anatomical information, as well as any additional information currently available on the CARTO mapping system, such as LAT or voltage, if so desired by the physician.
  • embodiments of the present invention encompass one or more of the following locating and mapping aspects: the first is intended to process locating information; the second processes sensed electrical information; the third integrates previously processed information; and the fourth processes the integrated information to generate a 3-D image of the heart chamber with the catheter superimposed thereon.
  • Catheters will be introduced percutaneously into the heart chambers. Each catheter will be trackable (using the previously described methodology). One or more reference catheters may be left in known landmarks, and a catheter will be used as the mapping/ablation catheter. The locations of the reference catheter(s) will be used to align the location of the heart chamber relative to its location on the "basic image.”
  • FIG. 14A is a pictorial illustration of a system S for performing exemplary catheterization procedures on a heart 12 of a living subject or patient 13, which is constructed and operative in accordance with a disclosed embodiment of the invention.
  • the system comprises a catheter 14, which is percutaneously inserted by an electrophysiologist or operator 16 through the patient's vascular system into a chamber or vascular structure of the heart 12.
  • the catheter 14 has a distal tip carrying a plurality of electrodes, and a control handle by which the operator 16 can manipulate to steer and deflect the catheter.
  • anatomic positional information i.e., of the distal portion of the catheter, and other functional images may then be prepared using a console 24, according to the methods disclosed in U.S. Patent Nos. 6,226,542 , and 6,301,496 , and in commonly assigned U.S. Patent No. 6,892,091 .
  • One commercial product embodying elements of the console 24 is the CARTO ® 3 System, available from Biosense Webster, Inc., 3333 Diamond Canyon Road, Diamond Bar, CA 91765, which performs catheter localization and produces 3-D electroanatomic maps of the heart as required. This system may be modified by those skilled in the art to embody the principles of the invention described herein.
  • Areas determined to be abnormal can be targeted and ablated by application of thermal energy, e.g., by passage of radiofrequency electrical current from a radiofrequency (RF) generator 25 of the console 24 through a cable 34 providing current to the catheter 14, including the ablation electrode 32 at the distal tip, which apply the radiofrequency energy to target tissue.
  • the console 24 typically contains one or more ablation power generators 25, a patient interface unit (PIU) 26, and one or more displays 27 and 28 to display 3-D maps and electrograms.
  • the catheter 14 is adapted to conduct ablative energy to the heart using radiofrequency energy. Such methods are disclosed in commonly assigned U.S. Patent Nos.
  • Ablation energy is conveyed from RF generator 25 to the heart 12 through the catheter electrodes via cable 34 which is connected to the console 24.
  • Pacing signals and other control signals may also be conveyed from the console 24 through the cable 34 and the catheter electrodes to the heart 12.
  • electrical signals for example, intracardiac ECG signals are conveyed from the heart 12 to the console 24 via the catheter electrodes.
  • ECG body surface patches including at least patches 38 are affixed to the patient's body. While the catheter electrodes are sensing intracardiac ECG signals, a plurality of electrodes in the ECG body surface patches 38 measure ECG signals across the heart and torso to provide reference signals for the intracardiac ECG signals measured by the catheter electrodes.
  • a magnetic field is generated around the patient 13, for example, by a location pad containing magnetic field generator coils 28 that is placed under the patient.
  • the magnetic fields generated by coils 28 generate electrical signals in coils of an electromagnetic (EM) sensor located in the distal tip of catheter 14.
  • the electrical signals are conveyed to the console 24 which includes a processor or "workstation” 22 that analyzes the signals so as to determine the coordinates of the position and orientation of catheter.
  • EM electromagnetic
  • the catheter electrodes are connected by lead wires (not shown) in the catheter and the cable 34 to current and voltage measurement circuitry in the processor 22.
  • the processor 22 and the console 24 are also connected by wires and a patch unit 31 to a plurality of body surface electrodes 30, which may be any type of body electrodes known in the art, such as button electrodes, needle electrodes, subcutaneous probes, or patch electrodes.
  • the body surface electrodes 30 are typically in galvanic contact with the body surface of the patient 13 and receive body surface currents therefrom.
  • the body surface electrodes 30 may be adhesive skin patches generically referred to as active current location (ACL patches) and may be placed at any convenient locations on the body surface of the patient 13 in the vicinity of the catheter 14.
  • ACL patches active current location
  • the console 24 comprises voltage generators which are connected to the ACL patches 30 via wires 35 and which the processor 22 uses to measure impedance of the patient tissue at the location of the patches 30. Accordingly, the console 24 uses both magnetic-based position sensing and impedance-based measurements for catheter localization, as described in U.S. Patent No. 7,536,218, issued to Govari et al. , and U.S. Patent No. 8,478383, issued to Bar-Tal et al. .
  • the catheter 14 is coupled to the console 24, which enables the operator 16 to observe and regulate the functions of the catheter 14.
  • the processor 22 and/or the console 24 include appropriate signal processing circuits and is coupled to drive a monitor 29 to display visual imagery including the 3-D electro anatomical maps.
  • the signal processing circuits typically receive, amplify, filter and digitize signals from the catheter 14, including signals generated by the catheter electrodes and EM sensor .
  • FIG. 14B is a schematic block diagram of the system S for displaying electrode acquisition sequence of a linear multi-polar catheter 100, in accordance with one embodiment of the present invention.
  • the catheter has electrodes or poles 1-5 which are positioned to detect intracardiac activation sequence, e.g., ventricular tachycardia VT in the right ventricle RV.
  • the local electrograms or signals acquired by poles 1-5 are received by EP signal processor 112 and processed (amplified, digitized, etc.) and sent to a control unit 122 with signal processor 118 and memory 119.
  • the signal processor 112 also identifies the particular electrodes and correlates the particular electrodes with their respective signals and/or local electrograms.
  • the system includes an ECG unit 115 (for example, with body surface electrode patches) for detecting the cardiac cycle in providing reference ECG signals.
  • the system also includes a timer 113 to process timing of occurrences of electrode acquisition, including recording the timing of such occurrences and determining a relative electrode acquisition timing for each electrode that is relative to an earliest occurrence of electrode acquisition within a single cardiac cycle.
  • the control unit 122 drives the monitor 120 to display visualization of catheter electrode acquisition, including a catheter electrode acquisition sequence in cine.
  • the display includes a 3-D electro anatomical map, including a graphical image of the anatomy mapped.
  • the catheter electrode acquisition sequence is displayed on the monitor 120, wherein the electrodes are visually designated, highlighted or otherwise distinguished, for example, by a color contrasting to a color of the distal tip, as signals are acquired, in the order or sequence of acquisition, within a cardiac cycle.
  • the intracardiac activation sequence e.g., VT arrows in the right ventricle RV
  • the signal travels clockwise from the ventricular apex VA, which is acquired earliest by pole 1, then pole 2, then pole 3, then pole 4 and then pole 5.
  • the acquisition sequence is displayed in animation or cine mode with the graphic image of pole 1 visually marked ( FIG. 15A ), followed by the graphic image of pole 2 visually marked ( FIG.
  • pole 1 upon acquisition may be displayed in color red
  • pole 2 upon acquisition may be displayed in orange
  • pole 3 upon acquisition may be displayed in yellow
  • pole 4 upon acquisition may be displayed in green
  • pole 5 upon acquisition may be displayed in blue.
  • nonsensing sections of the shaft between the poles may also be displayed in a manner consistent with the acquisition sequence.
  • shaft section S is visually marked both temporally and spatially between adjacent poles to help visually indicate the direction of acquisition sequence.
  • the color of each shaft section S may be blending of the colors of the adjacent poles.
  • shaft section S1 between poles 1 and 2 may be displayed in reddish orange, as a blending of the color red of pole 1 and the color orange of pole 2.
  • FIGS. 16A-16R illustrate an acquisition sequence where the acquisition sequence has a divergence or split, often indicating an incomplete block, as shown, for example, in FIG. 8A .
  • FIG. 16A earliest acquisition occurs at pole 7, followed by poles 6 and 8 as shown in FIG. 16E , followed by poles 5 and 9 in FIG. 161, and so on and so forth.
  • FIGS. 16B-16D and FIGS. 16F- 16H show directions of the acquisition sequence by visual marking of the shaft sections (in color red) between the poles (see arrows).
  • FIG. 17 illustrates a flowchart representing a method applied by the system S, including the control unit 122 and the processor 119 of FIG. 14 , in accordance with one embodiment of the present invention.
  • the method starts at block 200, with the processor 119 receiving and loading parameters of a physical model, as selected by a user, that define physical structure, configuration and properties of a sensing catheter at block 202, including, for example, the type of catheter (linear, circular/lasso, basket, etc.) and location of electrodes on the catheter relative to a reference on or in the catheter.
  • the system then starts electrode acquisition at block 203. This step may include, for example, the provision of a visible or audible indicator indicating the start of the acquisition.
  • electrode acquisition of electrical activity within a window of interest occurs in accordance with the discussion provided herein above regarding 3-D mapping, for example, in reference to FIGS. 5 and 6 .
  • the electrical activity detected by the electrodes of the catheter may be naturally occurring in the detected tissue in the region of interest or the electrical activity may result from a pacing signal sent to a suitable location in or near the heart chamber where the signal can travel to and/or throughout the region of interest in the heart chamber where the sensing catheter is located.
  • Applying a window of interest limits the recorded signals to only those relevant to the catheter(s) visually representing the electrical activation sequence.
  • the user selects a specific window of interest for this purpose per block 204.
  • the invention may use the current mapping window of interest already selected for the mapping phase, as described previously.
  • timing of occurrences of electrode acquisitions within a window of interest are recorded (block 206) and each occurrence of electrode acquisition is assigned a relative acquisition time that is relative to the timing of an earliest electrode acquisition (block 207).
  • pole 1 acquires earliest at time t(a), followed by pole 2 at later time t(b), followed by pole 3 at later time t(c), and followed by poles 4 and 5 at later times t(d) and t(e), respectively, times t(a)- t(e) are recorded (block 206), and relative acquisition times T(a)-T(e) are assigned (block 207).
  • identities of the acquiring Poles 1-5 on the catheter are obtained (block 205), for example, by identifying the lead wires on which the acquired signal was transmitted from the catheter to the electrophysiologic signal processor 112, and those identities of poles P1-P5, along with the above assigned relative times of electrode acquisition T(a)-T(e) are then correlated with each other (block 213) to generate a sequence of electrode acquistions (block 214).
  • An example of the processing of blocks 206, 207, 205, 213 and 214 for the catheter of FIGS. 15A-15E is shown in FIG. 18A .
  • the sequence is then displayed in an animation with a series of graphical images of at least the electrodes which providing visualization of the sequence or order of electrode acquisition per block 215.
  • the animation reveals an image in cine of five electrodes, with pole 1 highlighted ( FIG. 15A ), then pole 2 highlighted ( FIG. 15B ), then pole 3 highlighted ( FIG. 15C ), then pole 4 highlighted ( FIG. 15D ), then pole 5 highlighted ( FIG. 15E ).
  • FIG. 18B An example of the processing per blocks 206, 207, 205 and 204 is shown in FIG. 18B .
  • the resulting display sequence per block 215 provides an animation as shown in FIGS. 20A- 20C.
  • the animation speed may be adjusted.
  • Query 216 of FIG. 17 asks whether a user wishes to adjust the display sequence, for example, by selecting a time scale at which the animation is displayed, per block 218. If no, the processing ends at block 220. If yes, block 218 allows a user to make a selection, whereby, for example, the duration of the animation is increased by a selected factor N by multiplying each relative time T(i) by N, and a re-correlation is performed in block 214 in accordance with the selected time scale.
  • An example of the processing of blocks 214, 216 and 218 is shown in FIG. 18C .
  • block 219 allows the user to adjust or limit the ratio of visual representations to actual cardiac cycles in order to facilitate ease of viewing and avoid overlapping sequences of electrode acquisitions.
  • the user may select which electrode sequences are displayed, including whether the animation includes the acquisition sequence of every "nth" cardiac cycle.
  • a re-correlation is performed in block 214.
  • the animation may also reveal an image in cine of a catheter with five poles P1-P5, wherein the poles and sections of shaft S1-S5 between the poles are both highlighted in accordance with the acquisition sequence and direction of propagation. For example, if pole 3 acquires first, followed by poles 4 and 2, further followed by pole 5 and lastly by pole 1, the image in cine highlights the shaft sections S2 and S3 after highlighting pole 3 ( FIGS. 19A and 19B ) but before highlighting poles 4 and 2 ( FIG. 19C ).
  • the pole acquisition in this example is purposefully asymmetrical outwardly from pole 3 past poles 2 and 4, as pole 5 acquires prior to pole 1.
  • the image in cine thus appropriately highlights the shaft section S4 ( FIG. 19D ) after highlighting poles 4 and 2 ( FIG. 19C ) but before highlighting pole 5 ( FIG. 19E ), and further highlights the shaft section S1 ( FIG. 19F ) after highlighting pole 5 ( FIG. 19E ) but before highlighting pole 1 ( FIG. 19G ).
  • the shaft section designated per block 209 of FIG. 17 depends on the identity of two poles preceding and their sequence of acquisition. For example, if pole 2 acquires first, followed by pole 3, then the shaft section S2 between poles 2 and 3 is designated, with poles 2 and 3 treated the adjacent pole pair for the shaft section S2. For example, if pole 3 acquires first, followed simultaneously by poles 2 and 4, then shaft sections S2 and S4 are both designated, with poles 2 and 3 treated as the adjacent pole pair for the shaft section S2, and poles 3 and 4 treated as the adjacent pole pair for the shaft section S4. A relative time T is then assigned for each designated shaft section S per block 210 of FIG. 17 .
  • FIG. 18D An example of processing by block 209 and block 210 (applying Eqn. 1) for shaft sections S is shown in FIG. 18D , which also shows an example of processing by blocks 206, 207 and 205 for poles 1-5, and of processing by blocks 214 and 215 in correlating both the relative times T(i) and T(Si) for the poles and the shaft sections to provide a display sequence as shown in FIGS. 19A-19G .
  • T Sx 1 T earlier + T later ⁇ T earlier * 1 / m + 1
  • T Sx 2 T earlier + T later ⁇ T earlier * 2 / m + 1
  • T Sxm T earlier + T later ⁇ T earlier * m / m + 1
  • the assigned relative times T(Sxm) for each shaft subsection is weighted according to its location between the earlier- and later- acquiring adjacent poles, and the weighting is applied linearly and dependent on the plurality of subsections between the adjacent poles.
  • An example of the processing of block 209 designating and block 210 (applying Eqns. 2, 3 and 4) assigning relative times for the shaft subsections is shown in FIG. 18E , along with an example of the processing of blocks 206, 207, and 205 for the poles.
  • a display sequence as shown in FIGS. 21A-21I is generated by the system and method of the present invention.
  • the process includes spatial electrode localization.
  • electrode localization is obtained through measuring position of catheter with a magnetic field sensor typically located in a distal portion of the catheter, per block 208, and determining electrode location based on the magnetic-based measured position, per block 211.
  • Electrode localization is also obtained through impedance of each electrode, which is measured per block 212 to determine the location of the electrode based on an impedance map per block 217.
  • Location data (magnetic-based and/or impedance-based) is correlated with electrode identity per block 214 and relative electrode acquisition times to drive the display per block 215 in a manner where the graphic image of the catheter and its electrodes move dynamically corresponding to actual movements of the electrodes.
  • the method of visualization of the present invention accommodates hybrid and nonhybrid catheters.
  • the sensing catheter is a non-hybrid, magnetic-based catheter
  • localization of its electrodes are accomplished via blocks 208 and 209.
  • the sensing catheter is a hybrid catheter, an impedance map, and a calibration map on which the impedance map is based may be generated, as shown in the flowchart of FIG. 23
  • the hybrid catheter has an electromagnetic sensor 22 comprising three coils 24, 26 and 28 which generative electrical signals in response to three magnetic fields generated by magnetic field generator coils G1, G2 and G3, as driven by a magnetic field generator 119, as shown in FIG. 25 .
  • the coils G1, G2 and G3 are incorporated in a pad 117 that is situated under the patient. These signals are conveyed to a control unit 122, which analyzes the signals to determine the coordinates of catheter 20. Alternatively, the coils in the magnetic field sensor 22 may be driven to generate magnetic fields, which are detected by coils 28.
  • the catheter 20 also carries electrodes 30, 32 and 34, as shown in FIG. 24 , whose signals are received by impedance measurement circuitry 123 in control unit 122, as shown in FIG. 25 .
  • the control unit 122 is connected by wires to body surface patches via the EP signal processor 112 and body surface ECG unit 115. Impedances between the surface patches and the electrodes 30, 32 and 34 are measured according to methods described in U.S. Patent No. 7,869,865 to Govari, et al. .
  • Control unit 122 drives currents through one or more electric circuits, each of which comprises a catheter electrode, a respective body surface electrode, and the intervening body tissue.
  • the impedance between the electrode and patch in each circuit equals the voltage between the electrodes, divided by the current that flows through the circuit.
  • voltages may be applied across pairs of body surface electrodes, as described by the abovementioned U.S. Pat. No. 5,983,126 to Wittkampf . The respective voltage drops at the catheter electrodes are measured to determine the relative impedances.
  • FIG. 26 is a schematic, pictorial illustration of hybrid catheter 20 positioned within a chamber of heart 38 during generation of a calibration map, in accordance with an embodiment of the present invention.
  • the signals received from magnetic field sensor 22 are used to compute the position and orientation of the catheter at multiple locations, and, in particular, to derive the position coordinates of electrodes 30, 32, and 34 at these locations based on the magnetic coordinate measurements and the known displacement of the electrodes relative to sensor 22.
  • Impedance measurements are also made to electrodes 30, 32, and 34 at the different catheter locations, and these measurements are correlated with the electrode positions as determined by the magnetic position measurements. In this manner a calibration map is generated.
  • FIG. 27 is a schematic, pictorial illustration of a second catheter 58, which is inserted into heart 38 during or after generation of the calibration map, in accordance with an embodiment of the present invention.
  • impedance measurements taken at electrodes 60, 62, and 64 on the catheter are correlated with the impedance measurements that were previously recorded at known positions on the calibration map. In this manner, the coordinates of catheter 58 are determined accurately, notwithstanding the fluctuations and nonlinearities in the impedance of the subject's body.
  • FIG. 23 is a flowchart showing a method for generating and applying a calibration map, using tissue impedance, in accordance with an embodiment of the present invention.
  • the hybrid catheter 20 is inserted into a chamber of the heart 38.
  • the magnetic field sensor 22 is used to determine the position coordinates of the catheter, and thus find the specific locations of the catheter electrodes 30, 32 and 34. Impedance measurements at these catheter electrodes are then taken in an impedance measurement step 270.
  • the impedance measurements are correlated with the electrode positions determined in step 268.
  • a calibration map is generated in a mapping step 278.
  • the calibration map comprises a grid of coordinates, determined by magnetic sensing, with a set of impedance measurements (relative to each of the body-surface electrodes or to pairs of body-surface electrodes) recorded at each point in the grid.
  • the grid may be inverted, so that the map indicates the actual, calibrated position coordinates for each set of impedance measurements.
  • second catheter 58 is inserted into the body cavity, in an insertion step 280.
  • the second catheter 58 comprises electrodes 60, 62 and 64 that may be used to measure impedances, but it typically lacks magnetic field sensors.
  • impedances between the electrodes of the second catheter and the body-surface electrodes are measured.
  • position sensing step 284 the position coordinates of these catheter electrodes are determined by comparing the measured impedances with the calibration map. Based on the electrode positions, the positions of other elements of the second catheter may also be determined. Steps 282 and 284 may be repeated to continuously track catheter 58, until it is determined that the procedure is done, in a completion step 286.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Cardiology (AREA)
  • Physiology (AREA)
  • Artificial Intelligence (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Signal Processing (AREA)
  • Psychiatry (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
  • Surgical Instruments (AREA)

Claims (19)

  1. Procédé de visualisation d'informations électrophysiologiques détectées par des électrodes sur un cathéter (14), comprenant :
    la réception de données sur une configuration d'électrodes du cathéter (202, 214) ;
    l'enregistrement de temps d'acquisitions de signaux d'électrodes (203, 206) ;
    l'identification des électrodes avec l'acquisition de signaux (205) ;
    la désignation d'une acquisition la plus précoce des acquisitions de signaux d'électrodes en tant qu'acquisition de signaux d'électrodes de référence ;
    l'attribution d'un temps relatif à chaque temps enregistré d'acquisition de signaux d'électrodes par rapport à l'acquisition de signaux d'électrodes de référence (210) ;
    l'identification des électrodes avec une acquisition de signaux en fonction des données sur la configuration d'électrodes (213) ;
    l'obtention de données d'emplacement d'électrodes (208, 211, 212, 217) ;
    la mise en corrélation de temps relatifs attribués avec des électrodes identifiées et les données d'emplacement d'électrodes pour générer une séquence d'acquisitions de signaux d'électrodes (213, 214) ;
    la génération d'une représentation visuelle avec une image graphique de la position et de l'orientation des électrodes (215) en fonction des données sur la configuration d'électrodes et des données d'emplacement d'électrodes, et dans lequel des électrodes individuelles sont marquées visuellement pour représenter la séquence d'acquisitions de signaux d'électrodes (215) et dans lequel les électrodes se déplacent d'une manière dynamique correspondant aux mouvements réels des électrodes ; et
    l'attaque d'un affichage pour afficher la représentation visuelle.
  2. Procédé selon la revendication 1, dans lequel la génération d'une représentation visuelle comprend une pluralité d'images montrées en série pour représenter une progression de la séquence d'acquisitions de signaux d'électrodes (215).
  3. Procédé selon la revendication 2, dans lequel chaque image montre une électrode marquée visuellement différente (215).
  4. Procédé selon la revendication 2, dans lequel chaque image montre au moins une électrode marquée visuellement différente (215).
  5. Procédé selon la revendication 1, dans lequel le cathéter a des sections tige (S1 à S5), chaque section tige s'étendant entre deux électrodes adjacentes (P1 à P5), le procédé comprenant en outre :
    l'attribution d'un temps relatif à chaque section tige en fonction de temps relatifs de ses deux électrodes adjacentes (209, 210) ; et
    la mise en corrélation du temps relatif de chaque section tige avec les temps relatifs de ses deux électrodes adjacentes (213),
    dans lequel la génération d'une représentation visuelle comprend la fourniture d'une image graphique de chaque section tige, et le marquage visuel de chaque section tige individuelle en fonction de la séquence (215).
  6. Procédé selon la revendication 1, dans lequel l'identification des électrodes avec une acquisition de signaux comprend l'identification de fils conducteurs des électrodes (205).
  7. Procédé selon la revendication 1, comprenant en outre l'ajustement d'une échelle de temps de la représentation visuelle en réponse à une échelle de temps sélectionnée (218) de l'utilisateur.
  8. Procédé selon la revendication 1, dans lequel la génération d'une représentation visuelle de la séquence d'acquisitions d'électrodes comprend la séquence d'acquisitions d'électrodes d'un ou plusieurs cycles cardiaques (219).
  9. Procédé selon la revendication 8, dans lequel la génération d'une représentation visuelle comprend la séquence d'acquisitions d'électrodes d'un cycle cardiaque sélectionné (219) de l'utilisateur.
  10. Procédé selon la revendication 1, dans lequel le cathéter (14) comporte une pluralité d'électrodes, dans lequel chaque électrode est conçue pour acquérir un signal électrique.
  11. Procédé selon la revendication 10, dans lequel le cathéter comprend des sections tige (S1 à S5), chaque section tige s'étendant entre deux électrodes adjacentes (P1 à P5), le procédé comprenant en outre :
    l'attribution d'un temps relatif à chaque section tige en fonction de temps relatifs de ses deux électrodes d'acquisition adjacentes (209, 210) ; et
    la mise en corrélation du temps relatif de chaque section tige et des temps relatifs de ses deux électrodes d'acquisition adjacentes (213),
    dans lequel la génération d'une représentation visuelle comprend la fourniture d'une image graphique de chaque section tige, et le marquage visuel de sections tige individuelles en fonction de la séquence (215).
  12. Procédé selon la revendication 10, dans lequel l'identification d'électrodes acquérant un signal électrique comprend l'identification de fils conducteurs d'électrodes acquérant des signaux électriques.
  13. Procédé selon la revendication 10, dans lequel le cathéter comprend des sous-sections tige, chaque sous-section tige s'étendant entre deux électrodes adjacentes, le procédé comprenant en outre :
    l'attribution d'un temps relatif à chaque sous-section tige en fonction de temps relatifs de ses deux électrodes d'acquisition adjacentes et de son emplacement entre la paire adjacente ; et
    la mise en corrélation du temps relatif de chaque section tige et des temps relatifs de sa paire d'électrodes d'acquisition adjacentes,
    dans lequel la génération d'une représentation visuelle comprend la fourniture d'une image graphique de chaque section tige, et le marquage visuel de sections tige individuelles en fonction de la séquence.
  14. Procédé selon la revendication 13, dans lequel l'attribution d'un temps relatif à chaque sous-section tige comprend l'attribution d'un temps relatif pondéré.
  15. Procédé selon la revendication 14, dans lequel le temps relatif pondéré dépend de l'emplacement de la sous-section tige entre la paire d'électrodes d'acquisition adjacentes.
  16. Procédé selon la revendication 1 comprenant en outre :
    la réception de signaux acquis par les électrodes (203) ;
    et
    la génération d'une représentation visuelle de la séquence d'acquisitions de signaux d'électrodes dans lequel la représentation visuelle inclut des images graphiques des électrodes (215).
  17. Système de collecte et de visualisation d'informations électrophysiologiques, comprenant :
    un cathéter (14) doté d'électrodes conçues pour acquérir des signaux,
    une unité de traitement de signaux (112) configurée pour recevoir des acquisitions de signaux intracardiaques par une pluralité d'électrodes et pour recevoir des données sur une configuration d'électrodes du cathéter (14) et des données d'emplacement d'électrodes, et pour identifier les électrodes avec des acquisitions de signaux intracardiaques en fonction des données sur la configuration d'électrodes ;
    un minuteur (113) configuré pour chronométrer les acquisitions de signaux intracardiaques et pour identifier un temps de référence par rapport à une acquisition la plus précoce de signaux intracardiaques ;
    une unité de commande (122) configurée pour attribuer des temps relatifs aux acquisitions de signaux intracardiaques par rapport au temps de référence et pour mettre en corrélation des temps relatifs attribués avec des électrodes identifiées et les données d'emplacement d'électrodes pour générer une séquence d'acquisitions de signaux ; et
    un affichage (120) configuré pour afficher une image graphique de la position et de l'orientation des électrodes en fonction des données sur la configuration d'électrodes et des données d'emplacement d'électrodes, dans lequel des électrodes individuelles sont marquées visuellement pour représenter la séquence d'acquisitions de signaux d'électrodes et dans lequel les électrodes se déplacent d'une manière dynamique correspondant à des mouvements réels des électrodes.
  18. Système selon la revendication 17, dans lequel l'affichage (120) est un affichage configuré pour afficher la séquence d'acquisitions de signaux dans une série d'images graphiques d'au moins les électrodes.
  19. Système selon la revendication 18, dans lequel les sections tige (S1 à S5) entre les électrodes (P1 à P5) sont également marquées visuellement dans les images graphiques pour représenter la séquence d'acquisitions de signaux d'électrodes.
EP15202606.8A 2014-12-31 2015-12-23 Système et procédé de visualisation de données d'électrophysiologie Active EP3085303B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US14/587,964 US9662033B2 (en) 2014-12-31 2014-12-31 System and method for visualizing electrophysiology data

Publications (2)

Publication Number Publication Date
EP3085303A1 EP3085303A1 (fr) 2016-10-26
EP3085303B1 true EP3085303B1 (fr) 2023-03-01

Family

ID=55173748

Family Applications (1)

Application Number Title Priority Date Filing Date
EP15202606.8A Active EP3085303B1 (fr) 2014-12-31 2015-12-23 Système et procédé de visualisation de données d'électrophysiologie

Country Status (7)

Country Link
US (4) US9662033B2 (fr)
EP (1) EP3085303B1 (fr)
JP (1) JP6689604B2 (fr)
CN (2) CN116616778A (fr)
AU (1) AU2015268729B2 (fr)
CA (1) CA2916260A1 (fr)
RU (1) RU2015156669A (fr)

Families Citing this family (39)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9119633B2 (en) 2006-06-28 2015-09-01 Kardium Inc. Apparatus and method for intra-cardiac mapping and ablation
US11389232B2 (en) 2006-06-28 2022-07-19 Kardium Inc. Apparatus and method for intra-cardiac mapping and ablation
US8906011B2 (en) 2007-11-16 2014-12-09 Kardium Inc. Medical device for use in bodily lumens, for example an atrium
US9693832B2 (en) 2012-05-21 2017-07-04 Kardium Inc. Systems and methods for selecting, activating, or selecting and activating transducers
US9198592B2 (en) 2012-05-21 2015-12-01 Kardium Inc. Systems and methods for activating transducers
US10827977B2 (en) 2012-05-21 2020-11-10 Kardium Inc. Systems and methods for activating transducers
US10722184B2 (en) 2014-11-17 2020-07-28 Kardium Inc. Systems and methods for selecting, activating, or selecting and activating transducers
US10368936B2 (en) 2014-11-17 2019-08-06 Kardium Inc. Systems and methods for selecting, activating, or selecting and activating transducers
US10624554B2 (en) * 2016-01-14 2020-04-21 Biosense Webster (Israel) Ltd. Non-overlapping loop-type or spline-type catheter to determine activation source direction and activation source type
US11006887B2 (en) 2016-01-14 2021-05-18 Biosense Webster (Israel) Ltd. Region of interest focal source detection using comparisons of R-S wave magnitudes and LATs of RS complexes
EP3432780A4 (fr) 2016-03-21 2019-10-23 Washington University Visualisation en réalité virtuelle ou en réalité augmentée d'images médicales 3d
US11129574B2 (en) * 2016-12-12 2021-09-28 Biosense Webster (Israel) Ltd. Real time electroanatomical coloring of the heart
US10327851B2 (en) 2016-12-13 2019-06-25 Biosense Webster (Israel) Ltd. Method and apparatus for ablation planning and control
US10617317B2 (en) * 2017-02-27 2020-04-14 Biosense Webster (Israel) Ltd. Highlighting an electrode image according to an electrode signal
US11304644B2 (en) * 2017-03-07 2022-04-19 Biosense Webster (Israel) Ltd. 3-D electrophysiology heart simulation system and related methods
EP3576618B1 (fr) * 2017-04-14 2020-12-16 St. Jude Medical, Cardiology Division, Inc. Systèmes et procédés de détection, de mappage, d'interface et d'analyse indépendants de l'orientation
JP7257331B2 (ja) * 2017-05-09 2023-04-13 ボストン サイエンティフィック サイムド，インコーポレイテッド 手術室デバイス、方法、及びシステム
US10398346B2 (en) * 2017-05-15 2019-09-03 Florida Atlantic University Board Of Trustees Systems and methods for localizing signal resources using multi-pole sensors
CN110622254B (zh) * 2017-05-17 2024-04-05 圣犹达医疗用品心脏病学部门有限公司 用于标测局部激活时间的系统和方法
JP7170035B2 (ja) * 2017-09-18 2022-11-11 セント・ジュード・メディカル，カーディオロジー・ディヴィジョン，インコーポレイテッド 多次元カテーテルからの電気生理学的信号を分類するためのシステムおよび方法
US10792087B2 (en) * 2017-09-29 2020-10-06 Biosense Webster (Israel) Ltd. Highlighting region for re-ablation
US10398338B2 (en) 2017-10-06 2019-09-03 Florida Atlantic University Board Of Trustees Systems and methods for guiding a multi-pole sensor catheter to locate cardiac arrhythmia sources
US10575746B2 (en) * 2017-12-14 2020-03-03 Biosense Webster (Israel) Ltd. Epicardial mapping
US11164371B2 (en) * 2017-12-20 2021-11-02 Biosense Webster (Israel) Ltd. Marking a computerized model of a cardiac surface
EP3731722A4 (fr) * 2018-01-10 2022-02-09 AtriCure, Inc. Dispositif et accessoires pour un accès endoscopique percutané et systèmes d'ablation
US10856768B2 (en) * 2018-01-25 2020-12-08 Biosense Webster (Israel) Ltd. Intra-cardiac scar tissue identification using impedance sensing and contact measurement
US10665338B2 (en) * 2018-02-22 2020-05-26 Biosense Webster (Israel) Ltd. Automatic identification of multiple activation pathways
US10686715B2 (en) 2018-05-09 2020-06-16 Biosig Technologies, Inc. Apparatus and methods for removing a large-signal voltage offset from a biomedical signal
US11779280B2 (en) * 2018-06-29 2023-10-10 Biosense Webster (Israel) Ltd. Reference wires to remove noise and artifacts in cardiac mapping catheter
JP7175333B2 (ja) * 2018-09-10 2022-11-18 セント・ジュード・メディカル，カーディオロジー・ディヴィジョン，インコーポレイテッド 多次元カテーテルからの電気生理学的信号を表示するためのシステム及び方法
US11445935B2 (en) * 2018-11-26 2022-09-20 Biosense Webster (Israel) Ltd. Finding the origin of an arrythmia
CN111407279A (zh) * 2019-01-07 2020-07-14 四川锦江电子科技有限公司 一种基于神经网络的磁电结合定位追踪方法及装置
US11198004B2 (en) * 2019-04-11 2021-12-14 Biosense Webster (Israel) Ltd. Goal-driven workflow for cardiac arrhythmia treatment
US11452485B2 (en) * 2019-08-05 2022-09-27 Biosense Webster (Israel) Ltd. Electroanatomical map re-annotation
US11147497B2 (en) * 2019-11-28 2021-10-19 Biosense Webster (Israel) Ltd. Mapping local activation times for sinus and non-sinus cardiac cycles
US11311226B2 (en) * 2019-12-12 2022-04-26 Biosense Webster (Israel) Ltd. Detection of ventricular activity using unipolar and bipolar signals
US11517218B2 (en) * 2019-12-20 2022-12-06 Biosense Webster (Israel) Ltd. Selective graphical presentation of electrophysiological parameters
US20220160251A1 (en) 2020-11-25 2022-05-26 Biosense Webster (Israel) Ltd. Acquisition guidance for electroanatomical mapping
US11918383B2 (en) 2020-12-21 2024-03-05 Biosense Webster (Israel) Ltd. Visualizing performance of catheter electrodes

Family Cites Families (31)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA2018215A1 (fr) 1990-06-04 1991-12-04 Ross Manning Systeme de visualisation sur le coeur
IL116699A (en) * 1996-01-08 2001-09-13 Biosense Ltd Method of building a heart map
US5391199A (en) 1993-07-20 1995-02-21 Biosense, Inc. Apparatus and method for treating cardiac arrhythmias
US5558091A (en) 1993-10-06 1996-09-24 Biosense, Inc. Magnetic determination of position and orientation
WO1995010225A1 (fr) 1993-10-15 1995-04-20 Ep Technologies, Inc. Element a electrodes multiples de cartographie et d'ablation
US5876336A (en) 1994-10-11 1999-03-02 Ep Technologies, Inc. Systems and methods for guiding movable electrode elements within multiple-electrode structure
US6690963B2 (en) 1995-01-24 2004-02-10 Biosense, Inc. System for determining the location and orientation of an invasive medical instrument
US5697377A (en) 1995-11-22 1997-12-16 Medtronic, Inc. Catheter mapping system and method
US6177792B1 (en) 1996-03-26 2001-01-23 Bisense, Inc. Mutual induction correction for radiator coils of an objects tracking system
US5944022A (en) 1997-04-28 1999-08-31 American Cardiac Ablation Co. Inc. Catheter positioning system
US6226542B1 (en) 1998-07-24 2001-05-01 Biosense, Inc. Three-dimensional reconstruction of intrabody organs
US6301496B1 (en) 1998-07-24 2001-10-09 Biosense, Inc. Vector mapping of three-dimensionally reconstructed intrabody organs and method of display
US6157855A (en) 1999-04-02 2000-12-05 Siemens-Elema Ab Medical apparatus
US6172499B1 (en) 1999-10-29 2001-01-09 Ascension Technology Corporation Eddy current error-reduced AC magnetic position measurement system
US6892091B1 (en) 2000-02-18 2005-05-10 Biosense, Inc. Catheter, method and apparatus for generating an electrical map of a chamber of the heart
US6814733B2 (en) 2002-01-31 2004-11-09 Biosense, Inc. Radio frequency pulmonary vein isolation
US6997924B2 (en) 2002-09-17 2006-02-14 Biosense Inc. Laser pulmonary vein isolation
US7156816B2 (en) 2002-11-26 2007-01-02 Biosense, Inc. Ultrasound pulmonary vein isolation
US7107093B2 (en) * 2003-04-29 2006-09-12 Medtronic, Inc. Use of activation and recovery times and dispersions to monitor heart failure status and arrhythmia risk
US7869865B2 (en) 2005-01-07 2011-01-11 Biosense Webster, Inc. Current-based position sensing
DE102005005037B4 (de) * 2005-02-03 2012-02-02 Siemens Ag Einrichtung zur Aufnahme elektrophysiologischer Signale und zur Darstellung der Signale oder daraus ermittelter Signalinformationen
US7536218B2 (en) 2005-07-15 2009-05-19 Biosense Webster, Inc. Hybrid magnetic-based and impedance-based position sensing
US10398326B2 (en) * 2013-03-15 2019-09-03 The Regents Of The University Of California System and method of identifying sources associated with biological rhythm disorders
US8959442B2 (en) * 2010-06-11 2015-02-17 Microsoft Corporation Memory allocation visualization for unmanaged languages
US8478383B2 (en) 2010-12-14 2013-07-02 Biosense Webster (Israel), Ltd. Probe tracking using multiple tracking methods
US8768465B2 (en) * 2012-02-17 2014-07-01 Medtronic, Inc. Criteria for optimal electrical resynchronization derived from multipolar leads or multiple electrodes during biventricular pacing
WO2013192459A1 (fr) * 2012-06-20 2013-12-27 Intermountain Invention Management, Llc Systèmes et méthodes de traitement de fibrillation auriculaire
US8577450B1 (en) * 2012-07-23 2013-11-05 Biosense Webster (Israel) Ltd. Graphic interface for multi-spine probe
US9486151B2 (en) * 2013-06-12 2016-11-08 Medtronic, Inc. Metrics of electrical dyssynchrony and electrical activation patterns from surface ECG electrodes
US9642674B2 (en) * 2013-09-12 2017-05-09 Biosense Webster (Israel) Ltd. Method for mapping ventricular/atrial premature beats during sinus rhythm
US9717429B2 (en) * 2013-10-31 2017-08-01 St. Jude Medical, Cardiology Division, Inc. System and method for analyzing biological signals and generating electrophyisology maps

Also Published As

Publication number Publication date
EP3085303A1 (fr) 2016-10-26
JP2016123870A (ja) 2016-07-11
US20190008404A1 (en) 2019-01-10
US10582872B2 (en) 2020-03-10
US10105074B2 (en) 2018-10-23
US20200205686A1 (en) 2020-07-02
US20170231517A1 (en) 2017-08-17
CN116616778A (zh) 2023-08-22
AU2015268729A1 (en) 2016-07-14
US11839481B2 (en) 2023-12-12
US20160183824A1 (en) 2016-06-30
CA2916260A1 (fr) 2016-06-30
AU2015268729B2 (en) 2019-11-28
RU2015156669A (ru) 2017-07-06
US9662033B2 (en) 2017-05-30
JP6689604B2 (ja) 2020-04-28
RU2015156669A3 (fr) 2019-06-24
CN105726010A (zh) 2016-07-06

Similar Documents

Publication Publication Date Title
US11839481B2 (en) System and method for visualizing electrophysiology data
US11278228B2 (en) Identification and visualization of cardiac activation sequence in multi-channel recordings
US10441188B2 (en) Automatic display of earliest LAT point
EP2689722B1 (fr) Un appareil pour cartographier l'activité électrique cardiaque
US8923959B2 (en) Methods and system for real-time cardiac mapping
US20170189134A1 (en) Method for mapping ventricular/atrial premature beats during sinus rhythm
US11198004B2 (en) Goal-driven workflow for cardiac arrhythmia treatment
US20140058246A1 (en) System and methods for real-time cardiac mapping
US9706937B2 (en) Ventricular electrical activity indicator
Schmitt et al. Recent advances in cardiac mapping techniques
US10149626B1 (en) Methods and systems for mapping and ablation of cardiac arrhythmias comprising atrial flutter
US20240285216A1 (en) Local ecg annotation visualization
US20240164686A1 (en) Three-dimensional display of a multi-electrode catheter and signals acquired over time
US20230337931A1 (en) System and method for mapping repolarization of cardiac tissue
Skadsberg et al. Cardiac mapping technology
US20240115312A1 (en) Detection of electrophysiological (ep) conduction gaps in ablation line
Ueda et al. Fundamentals of Catheter Three-Dimensional Mapping Systems
Ndrepepa Three-dimensional electroanatomic mapping systems
Glover et al. Electroanatomic Mapping
Liem ELECTROANATOMICAL MAPPING USING THE CARTO® SYSTEM
Namboodiri et al. Contact and Noncontact Electroanatomical Mapping
Shenasa et al. Mapping of Macroreentrant Atrial Tachycardias

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

AX Request for extension of the european patent

Extension state: BA ME

17P Request for examination filed

Effective date: 20170426

RBV Designated contracting states (corrected)

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: REQUEST FOR EXAMINATION WAS MADE

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: EXAMINATION IS IN PROGRESS

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: EXAMINATION IS IN PROGRESS

17Q First examination report despatched

Effective date: 20201222

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: EXAMINATION IS IN PROGRESS

RAP3 Party data changed (applicant data changed or rights of an application transferred)

Owner name: BIOSENSE WEBSTER (ISRAEL) LTD.

REG Reference to a national code

Ref country code: DE

Ref legal event code: R079

Ref document number: 602015082636

Country of ref document: DE

Free format text: PREVIOUS MAIN CLASS: A61B0005042000

Ipc: A61B0005287000

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: GRANT OF PATENT IS INTENDED

RIC1 Information provided on ipc code assigned before grant

Ipc: A61B 5/339 20210101ALI20221101BHEP

Ipc: A61B 5/333 20210101ALI20221101BHEP

Ipc: A61B 5/316 20210101ALI20221101BHEP

Ipc: A61B 5/287 20210101AFI20221101BHEP

INTG Intention to grant announced

Effective date: 20221124

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE PATENT HAS BEEN GRANTED

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: CH

Ref legal event code: EP

Ref country code: AT

Ref legal event code: REF

Ref document number: 1550460

Country of ref document: AT

Kind code of ref document: T

Effective date: 20230315

REG Reference to a national code

Ref country code: DE

Ref legal event code: R096

Ref document number: 602015082636

Country of ref document: DE

REG Reference to a national code

Ref country code: IE

Ref legal event code: FG4D

REG Reference to a national code

Ref country code: LT

Ref legal event code: MG9D

REG Reference to a national code

Ref country code: NL

Ref legal event code: MP

Effective date: 20230301

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: RS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: NO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230601

Ref country code: LV

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: LT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: HR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: ES

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

REG Reference to a national code

Ref country code: AT

Ref legal event code: MK05

Ref document number: 1550460

Country of ref document: AT

Kind code of ref document: T

Effective date: 20230301

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: PL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: NL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: GR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230602

Ref country code: FI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SM

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: RO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: PT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230703

Ref country code: EE

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: CZ

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: AT

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: IS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230701

REG Reference to a national code

Ref country code: DE

Ref legal event code: R097

Ref document number: 602015082636

Country of ref document: DE

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 20231102

Year of fee payment: 9

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SI

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: DK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: IT

Payment date: 20231110

Year of fee payment: 9

Ref country code: FR

Payment date: 20231108

Year of fee payment: 9

Ref country code: DE

Payment date: 20231031

Year of fee payment: 9

26N No opposition filed

Effective date: 20231204

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LU

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20231223

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

REG Reference to a national code

Ref country code: BE

Ref legal event code: MM

Effective date: 20231231

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230301

Ref country code: LU

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20231223

REG Reference to a national code

Ref country code: IE

Ref legal event code: MM4A

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20231223

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: BE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20231231